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WO2003052091A1 - Matrices proteiques modifiees de facteur de croissance pour des applications en genie tissulaire - Google Patents

Matrices proteiques modifiees de facteur de croissance pour des applications en genie tissulaire Download PDF

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Publication number
WO2003052091A1
WO2003052091A1 PCT/US2002/041114 US0241114W WO03052091A1 WO 2003052091 A1 WO2003052091 A1 WO 2003052091A1 US 0241114 W US0241114 W US 0241114W WO 03052091 A1 WO03052091 A1 WO 03052091A1
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WIPO (PCT)
Prior art keywords
matrix
pth
fusion peptide
domain
peptide
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PCT/US2002/041114
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English (en)
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WO2003052091A8 (fr
Inventor
Jeffrey A. Hubbell
Matthias Lutolf
Jason Schense
Anna Jen
Original Assignee
Eidgenossisch Technische Hochschule Zurich
Universitat Zurich
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Priority claimed from US10/024,918 external-priority patent/US20020168718A1/en
Priority claimed from PCT/EP2002/012458 external-priority patent/WO2003040235A1/fr
Priority claimed from US10/323,046 external-priority patent/US7601685B2/en
Priority to KR1020047009700A priority Critical patent/KR100925070B1/ko
Priority to BRPI0215192A priority patent/BRPI0215192B8/pt
Priority to AU2002358272A priority patent/AU2002358272B2/en
Priority to JP2003552958A priority patent/JP4560291B2/ja
Priority to CA002470419A priority patent/CA2470419A1/fr
Application filed by Eidgenossisch Technische Hochschule Zurich, Universitat Zurich filed Critical Eidgenossisch Technische Hochschule Zurich
Priority to DE60225185T priority patent/DE60225185T2/de
Priority to EP02792510A priority patent/EP1465989B1/fr
Priority to MXPA04006021A priority patent/MXPA04006021A/es
Publication of WO2003052091A1 publication Critical patent/WO2003052091A1/fr
Publication of WO2003052091A8 publication Critical patent/WO2003052091A8/fr
Priority to NO20043031A priority patent/NO331726B1/no
Priority to HK04110140A priority patent/HK1067147A1/xx

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
    • A61L27/225—Fibrin; Fibrinogen
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
    • A61L27/227—Other specific proteins or polypeptides not covered by A61L27/222, A61L27/225 or A61L27/24
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P19/00—Drugs for skeletal disorders
    • A61P19/08—Drugs for skeletal disorders for bone diseases, e.g. rachitism, Paget's disease
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P43/00—Drugs for specific purposes, not provided for in groups A61P1/00-A61P41/00
    • C—CHEMISTRY; METALLURGY
    • C07—ORGANIC CHEMISTRY
    • C07K—PEPTIDES
    • C07K14/00—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof
    • C07K14/435—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof from animals; from humans
    • C07K14/575—Hormones
    • C07K14/635—Parathyroid hormone, i.e. parathormone; Parathyroid hormone-related peptides
    • C—CHEMISTRY; METALLURGY
    • C07—ORGANIC CHEMISTRY
    • C07K—PEPTIDES
    • C07K2319/00—Fusion polypeptide

Definitions

  • the invention relates to fusion proteins or peptides which contain PTH and an amino acid sequence that allows for binding interactions to matrices and to the use of fusion proteins or peptides in tissue repair and regeneration, and in the controlled release of PTH.
  • Parathyroid hormone is an 84 amino acid peptide that is made and secreted by the parathyroid gland. This hormone plays a primary role in controlling serum calcium levels through its action on various tissues, including bone. Studies in human with various forms of PTH have demonstrated an anabolic effect on bone, what makes them interesting for treatment of osteoporosis and related bone disorders (U.S. Patent No. 5,747,456 to Chorev, et al. and WO 00/10596 to Eli Lilly & Co.). The parathyroid hormone acts on cells by binding to a cell surface receptor. This receptor is known to be found on osteoblasts, the cells that are responsible for forming new bone.
  • PTH When PTH binds to a mesenchymal stem cell, the cell is induced to differentiate into a preosteoblast. Thus, by adding PTH to the system, there is an increase in the preosteoblast population. However, these preosteoblast cells have the PTH receptor as well, and the subsequent binding of the PTH to the receptor on these cells leads to a different response.
  • PTH binds to the preosteoblast, it results in two separate consequences that lead to bone resorption. First, it inhibits the further differentiation of the preosteoblasts into osteoblasts. Second, it increases the secretion of Interluekin 6 (IL-6) from the preosteoblasts.
  • IL-6 Interluekin 6
  • IL-6 both inhibits preosteoblast differentation as well as increases preosteoclast differentiation into osteoclasts.
  • This dual response from the cells within the osteoblast lineage is what provides the complex reaction between bone remodelling and PTH exposure. If PTH is dosed periodically for short periods of time, then the mesenchymal stem cells are induced to differentiate into osteoblasts. The short dosing periods then prevent the newly formed preosteoblasts from producing IL-6, preventing activation of the osteoclasts. Therefore, during the intervals of dosing, these newly formed preosteoblasts can further differentiate into osteoblasts, resulting in bone formation.
  • Natural cell in-growth matrices are subject to remodeling by cellular influences, all based on proteolysis, e.g. by plasmin (degrading fibrin) and matrix metalloproteinases (degrading collagen, elastin, etc.). Such degradation is highly localized and occurs only upon direct contact with the migrating cell. In addition, the delivery of specific cell signaling proteins such as growth factors is tightly regulated. In the natural model, macroporous cell in-growth matrices are not used, but rather microporous matrices that the cells can degrade, locally and upon demand, as the cells migrate into the matrix. Due to concerns regarding immunogenicity, expensive production, limited availability, batch variability and purification, matrices based on synthetic precursor molecules, such as modified polyethyleneglycol, have been developed for tissue regeneration in and/or on the body.
  • synthetic precursor molecules such as modified polyethyleneglycol
  • PTH has a direct anabolic effect on the osteoblast cell lineage, it should have a strong potential to heal bone defects in addition to influencing bone density if presented appropriately within a defect site.
  • the defect Once the defect has been filled with preosteoblasts, if the PTH signal is turned off, the newly formed preosteoblasts can then differentiate into osteoblasts and begin converting the wound bed, first into woven bone tissue and then into a mature bone structure. It is therefore an object of the present invention to provide PTH in a form that can be bound to a matrix for tissue repair, regeneration, and remodeling. It is a further object to present a PTH in a form suitable for topical or local administration to a patient to heal bone defects.
  • Fusion peptides which contain a parathyroid hormone (PTH) in one domain and a substrate domain capable of being covalently crosslinked to a matrix in another domain and matrices and kits which contain such fusion proteins or peptides are disclosed herein.
  • Fusion proteins covalently bind to natural or synthetic materials to form matrices, which may be used to heal bone defects.
  • all of the components for forming the matrix are applied to a bone defect and the matrix is formed at the site of application.
  • the fusion peptide can be incorporated into the matrix such that either the fusion peptide as a whole or just the respective PTH sequence of the first domain is released by degradation of the matrix, by enzymatic and/or hydrolytic action.
  • the fusion peptide can contain a degradable linkage between the first and the second domain that contains hydrolytic or enzymatic cleavage sites.
  • the fusion peptide contains PTH in one domain, a substrate domain capable of being covalently crosslinked to a matrix in a second domain, and a degradation site between the first and the second domain.
  • the PTH is human PTH, although PTH from other sources, such as bovine PTH, may be suitable.
  • the PTH can be PTH 1-84 (native), PTH 1-38, PTH 1-34, PTH 1-31, or PTH 1-25, or any modified or allelic versions of PTH exhibiting properties, i.e. bone formation, similar to the foregoing.
  • the degradation site allows the rate of delivery to be varied at different locations within the matrix depending on cellular activity at that location and/or within the matrix. Additional benefits include the lower total drug dose within the delivery system, and spatial regulation of release which permits a greater percentage of the drug to be released at the time of greatest cellular activity.
  • FIGURE 1 is a fluorescence detection chromatogram of plasmin- degraded peptide-containing fibrin gels and free peptide. Size exclusion chromatography of a degraded fibrin gel with the a 2 PI 1-7 -ATIIIi 2 i-i 3 peptide incorporated ( - ), with the same peptide free added to the degraded fibrin gel containing incorporated peptide ( " ), and free peptide alone (- -), are shown. The N-terminal leucine residue was dansylated (abbreviated dL).
  • FIGURE 2 is a graph of the incorporation of dLNQEQVSPLRGD (SEQ ID NO: 1) into fibrin gels with exogenous Factor XIII added. When 1 U/mL was added, the level of incorporation increased such that more than 25 mol peptide/mol fibrinogen could be achieved.
  • FIGURE 3 is a graph of the incorporation of the bidomain peptide, dLNQEQVSPLRGD (SEQ ID NO: 1) into undiluted fibrin glue.
  • Three separate kits were tested and in each case a high level of incorporation could be observed, reaching 25 mol peptide/mol fibrinogen.
  • the concentration of exogenous peptide required for maximal incorporation was at least 5 mM, possibly due to diffusion limitations within the highly dense fibrin matrix that is created.
  • the level of incorporation was very consistent, with each kit providing a similar incorporation profile.
  • the natural matrices are biocompatible and biodegradable and can be formed in vitro or in vivo, at the time of implantation.
  • PTH can be incorporated into the matrices and retain its full bioactivity.
  • PTH can be releasably incorporated, using techniques that provide control over how and when and to what degree the PTH is released, so that the matrix can be used for tissue repair directly or indirectly, using the matrix as a controlled release vehicle.
  • Biomaterial as generally used herein refers to a material intended to interface with biological systems to evaluate, treat, augment, or replace any tissue, organ or function of the body depending on the material either permanently or temporarily.
  • biomaterial and matrix are used synonymously herein and mean a crosslinked polymeric network which, depending of the nature of the matrix, can be swollen with water but not dissolved in water, i.e. form a hydrogel which stays in the body for a certain period of time fulfilling certain support functions for traumatized or defect hard tissue.
  • PTH fusion peptide refers to a peptide which contains at least a first and a second domain.
  • One domain contains a PTH (native or truncated forms, in particular PTH 1-34) and the other domain contains a substrate domain for being crosslinked to a matrix.
  • An enzymatic or hydrolytic degradation site can also be present between the first and the second domain.
  • “Strong nucleophile” as generally used herein refers to a molecule which is capable of donating an electron pair to an electrophile in a polar- bond forming reaction.
  • the strong nucleophile is more nucleophilic than water at physiologic pH. Examples of strong nucleophiles are thiols and amines.
  • Conjugated unsaturated bond refers to the alternation of carbon-carbon, carbon-heteroatom or heteroatom-heteroatom multiple bonds with single bonds, or the linking of a functional group to a macromolecule, such as a synthetic polymer or a protein. Such bonds can undergo addition reactions.
  • Conjugated unsaturated group refers to a molecule or a region of a molecule, which contains an alternation of carbon- carbon, carbon-heteroatom or heteroatom-heteroatom multiple bonds with single bonds, which has a multiple bond which can undergo addition reactions.
  • conjugated unsaturated groups include, but are not limited to vinyl sulfones, acrylates, acrylamides, quinones, and vinylpyridiniums, for example, 2- or 4-vinylpyridinium and itaconates.
  • Synthetic precursor molecules as generally used herein refers to molecules which do not exist in nature.
  • “Naturally occurring precursor components or polymers” as generally used herein refers to molecules which could be found in nature. "Functionalize” as generally used herein refers to modifying a molecule in a manner that results in the attachment of a functional group or moiety.
  • a molecule may be functionalized by the introduction of a molecule which makes the molecule a strong nucleophile or a conjugated unsaturation.
  • a molecule for example PEG, is functionalized to become a thiol, amine, acrylate, or quinone. Proteins, in particular, may also be effectively functionalized by partial or complete reduction of disulfide bonds to create free thiols.
  • Frunctionality refers to the number of reactive sites on a molecule.
  • Branching points refers to the number of arms extending from one point in the molecule.
  • Adhesion site or cell attachment site refers to a peptide sequence to which a molecule, for example, an adhesion- promoting receptor on the surface of a cell, binds.
  • adhesion sites include, but are not limited to, the RGD sequence from fibronectin, and the YIGSR (SEQ ID NO:2) sequence from laminin.
  • adhesion sites are incorporated into the biomaterial by including a substrate domain crosslinkable to a matrix.
  • Biological activity as generally used herein refers to functional events mediated by a protein of interest. In some embodiments, this includes events assayed by measuring the interactions of a polypeptide with another polypeptide. It also includes assaying the effect which the protein of interest has on cell growth, differentiation, death, migration, adhesion, interactions with other proteins, enzymatic activity, protein phosphorylation or dephosphorylation, transcription, or translation.
  • Sensitive biological molecule refers to a molecule that is found in a cell, or in a body, or which can be used as a therapeutic for a cell or a body, which may react with other molecules in its presence.
  • sensitive biological molecules include, but are not limited to, peptides, proteins, nucleic acids, and drugs. Biomaterials can be made in the presence of sensitive biological materials, without adversely affecting the sensitive biological materials.
  • Regularate as generally used herein means to grow back a portion or all of something, such as hard tissue, in particular bone.
  • Multifunctional refers to more than one electrophilic and /or nucleophilic functional group per molecule (i.e. monomer, oligo-and polymer).
  • Self selective reaction means that the first precursor component of a composition reacts much faster with the second precursor component of the composition and vice versa than with other compounds present in a mixture or at the site of the reaction.
  • the nucleophile preferentially binds to a electrophile and an electrophile preferentially binds to a strong nucleophile, rather than to other biological compounds.
  • Cross-linking as generally used herein means the formation of covalent linkages. However, it may also refer to the formation of non- covalent linkages, such as ionic bonds, or combinations of covalent and non- covalent likages.
  • Polymeric network as generally used herein means the product of a process in which substantially all of the monomers, oligo- or polymers are bound by intermolecular covalent linkages through their available functional groups to result in one huge molecule.
  • physiological means conditions as they can be found in living vertebrates.
  • physiological conditions refer to the conditions in the human body such as temperature, pH, etc.
  • Physiological temperatures means in particular a temperature range of between 35°C to 42°C, preferably around 37°C.
  • Crosslink density refers to the average molecular weight between two crosslinks (M c ) of the respective molecules.
  • “Equivalent weight” as generally used herein refers to mmol of functional group/g of substance.
  • “Swelling” as generally used herein refers to the increase in volume and mass by uptake of water by the biomaterial. The terms” water-uptake” and “swelling” are used synonymously throughout this application.
  • “Equilibrium state” as generally used herein as the state in which a hydrogel undergoes no mass increase or loss when stored under constant conditions in water.
  • the matrix is formed by crosslinking ionically, covalently, or by combinations thereof precursor molecules to a polymeric network or by swelling one or more polymeric materials, i.e. matrices, to form a polymeric network having sufficient inter-polymer spacing to allow for ingrowth or migration into the matrix of cells.
  • the matrix is formed of proteins, preferably proteins naturally present in the patient into which the matrix is to be implanted.
  • a particularly preferred matrix protein is fibrin, although matrices made from other proteins, such as collagen and gelatin can also be used. Polysaccharides and glycoproteins may also be used to form the matrix. It is also possible to use synthetic polymers which are crosslinkable by ionic or covalent binding.
  • Fibrin is a natural material which has been reported for several biomedical applications. Fibrin has been described as material for cell ingrowth matrices in U.S. Patent No. 6,331 ,422 to Hubbell et al. Fibrin gels have been used as sealants because of its ability to bind to many tissues and its natural role in wound healing. Some specific applications include use as a sealant for vascular graft attachment, heart valve attachment, bone positioning in fractures and tendon repair (Sierra, D.H., Journal of Biomaterials Applications, 7:309-352 (1993)).
  • fibrinogen The process by which fibrinogen is polymerized into fibrin has also been characterized.
  • a protease cleaves the dimeric fibrinogen molecule at the two symmetric sites.
  • proteases There are several possible proteases than can cleave fibrinogen, including thrombin, reptilase, and protease III, and each one severs the protein at a different site (Francis, et ah, Blood Cells, 19:291-307, 1993).
  • thrombin thrombin
  • reptilase and protease III
  • ⁇ 2-plasmin inhibitor (Aoki, N., Progress in Cardiovascular Disease, 21:267-286, 1979). This molecule acts by crosslinking to the ⁇ chain of fibrin through the action of Factor XHIa (Sakata, et ah, Journal of
  • the ⁇ 2-plasmin inhibitor contains a glutamine substrate.
  • the exact sequence has been identified as NQEQNSPL (SEQ ID NO: 12), with the first glutamine being the active amino acid for crosslinking.
  • bi-domain peptides which contain a factor XHIa substrate sequence and a bioactive peptide sequence, can be cross-linked into fibrin gels and that this bioactive peptide retains its cellular activity in vitro (Schense, J.C., et al. (1999) Bioconj. Chem. 10:75-81). Synthetic matrices
  • Crosslinking reactions for forming synthetic matrices for application in the body include (i) free-radical polymerization between two or more precursors containing unsaturated double bonds, as described in Hern et al., J Biomed. Mater. Res. 39:266-276 (1998), (ii) nucleophilic substitution reaction such as e.g. between a precursor including an amine group and a precursor including a succinimidyl group as disclosed in U.S. Patent No. 5,874,500 to Rhee et ah, (iii) condensation and addition reactions and (iv) Michael type addition reaction between a strong nucleophile and a conjugated unsaturated group or bond (as a strong electrophile).
  • Michael type addition reactions are described in WO 00/44808 to Hubbell et ah, the content of which is incorporated herein by reference. Michael type addition reactions allow for in situ crosslinking of at least a first and a second precursor component under physiological conditions in a self-selective manner, even in the presence of sensitive biological materials.
  • one of the precursor components has a functionality of at least two, and at least one of the other precursor components has a functionality greater than two, the system will self- selectively react to form a cross-linked three dimensional biomaterial.
  • conjugated unsaturated groups or conjugated unsaturated bonds are acrylates, vinylsulfones, methacrylates, acrylamides, methacrylamides, acrylonitriles, vinylsulfones, 2- or 4-vinylpyridinium, maleimides, or quinones.
  • the nucleophilic groups are preferably thiol-groups, amino-groups or hydroxyl-groups.
  • Thiol groups are substantially more reactive than unprotonated amine groups.
  • the pH is an important in this consideration: the deprotonated thiol is substantially more reactive than the protonated thiol. Therefore, the addition reactions involving a conjugated unsaturation, such as an acrylate or a quinone, with a thiol to convert two precursor components into a matrix will often be best carried out most quickly and self-selectively at a pH of approximately 8.
  • Suitable first and second precursor molecules include proteins, peptides, polyoxyalkylenes, poly(vinyl alcohol), poly(ethylene-co-vinyl alcohol), poly(acrylic acid), poly(ethylene-co-acrylic acid), poly(ethyloxazoline), poly( vinyl pyrrolidone), poly(ethylene-co-vinyl pyrrolidone), poly(maleic acid), poly(ethylene-co-maleic acid), poly(acrylamide), and poly(ethylene oxide)-co-poly(propylene oxide) block copolymers.
  • a particularly preferred precursor molecule is polyethylene glycol.
  • Polyethylene glycol provides a convenient building block.
  • a strong nucleophile such as a thiol
  • a conjugated structure such as an acrylate or a vinylsulfone.
  • a PEG component can be reacted with a non-PEG component, and the molecular weight or hydrophilicity of either component can be controlled to manipulate the mechanical characteristics, the permeability, and the water content of the resulting biomaterial.
  • peptides provide a very convenient building block. It is straightforward to synthesize peptides that contain two or more cysteine residues, and this component can then readily serve as the first precursor component with nucleophilic groups. For example, a peptide with two free cysteine residues will readily form a matrix when mixed with a PEG tri- vinylsulfone (a PEG having three arms with vinylsulfones at each of its arms) at physiological or slightly higher pH (e.g., 8 to 9). The gelation can also proceed well at even higher pH, but at the potential expense of self- selectivity.
  • PEG tri- vinylsulfone a PEG having three arms with vinylsulfones at each of its arms
  • slightly higher pH e.g. 8 to 9
  • the two liquid precursor components react over a period of a few minutes to form an elastic gel, consisting of a network of PEG chains, bearing the nodes of the network, with the peptides as connecting links.
  • the peptides can be selected as protease substrates, so as to make the network capable of being infiltrated and degraded by cells, as is done in a protein-based network, such as in a fibrin matrix.
  • the sequences in the domains are substrates for enzymes that are involved in cell migration (e.g., as substrates for enzymes such as collagenase, plasmin, metalloproteinase (MMP) or elastase), although suitable domains are not be limited to these sequences.
  • One particularly useful sequence is a substrate for the enzyme plasmin (see Examples).
  • the degradation characteristics of the gels can be manipulated by changing the details of the peptide that serves as the cross-linking nodes.
  • it is possible to make the gel degrade faster or slower in response to such an enzyme simply by changing the amino acid sequence so as to alter the K m or k cat , or both, of the enzymatic reaction.
  • One can thus make a biomaterial that is biomimetic, in that it is capable of being remodeled by the normal remodeling characteristics of cells For example, such a study shows substrate sites for the important protease plasmin.
  • the gelation of the PEG with the peptide is self-selective.
  • biofunctional agents can be incorporated into the matrix to provide chemical bonding to other species (e.g., a tissue surface).
  • Having protease substrates incorporated into the matrix is important when the matrix is formed from PEG vinylsulfone.
  • matrices formed from the reaction of PEG acrylates and PEG thiols matrices formed from PEG vinylsulfones and PEG thiols do not contain hydrolytically degradable bonds. Therefore, the incorporation of protease substrates allows the matrix to degrade degrade in the body.
  • the synthetic matrices are operationally simple to form. Two liquid precursors are mixed; one precursor contains a precursor molecule with nucleophilic groups and the other precursor molecule contains the electrophilic groups.
  • Physiological saline can serve as the solvent. Minimal heat is generated by reaction. Therefore, the gelation can be carried out in vivo or in vitro, in direct contact with tissue, without untoward toxicity.
  • polymers other than PEG may be used, either telechelically modified or modified on their side groups.
  • the rate of cell ingrowth or migration of cells into the matrix in combination with an adapted degradation rate of the matrix is crucial for the overall healing response.
  • the potential of hydrolytically non-degradable matrices to become invaded by cells is primarily a function of network density. If the existing space between branching points or nodes is too small in relation to the size of the cells or if the rate of degradation of the matrix, which results in creating more space within the matrix, is too slow, a very limited healing response will be observed.
  • Healing matrices found in nature, as e.g. fibrin matrices, which are formed as a response to injury in the body are known to consist of a very loose network which very easily can be invaded by cells. The infiltration is promoted by ligands for cell adhesion which are an integrated part of the fibrin network.
  • Matrices made from synthetic hydrophilic precursor molecules like polyethene glycol, swell in aqueous environment after formation of the polymeric network.
  • the starting concentration of the precursor molecules must be sufficiently high. Under such conditions, swelling after network formation would not take place, and the necessary starting concentrations would lead to matrices too dense for cell infiltration when the matrix is not degradable in aqueous environment.
  • swelling of the polymeric network is important to enlarge and widen the space between the branching points.
  • hydrogels made from the same synthetic precursor molecules such as a four arm PEG vinylsulfone and a peptide with SH groups, swell to the same water content in equilibrium state. This means that the higher the starting concentration of the precursor molecules are, the higher the end volume of the hydrogel is when it reaches its equilibrium state. If the space available in the body is too small to allow for sufficient swelling and in particular if the linkage formed from the precursor components are not hydrolytically degradable, the rate of cell infiltration and the healing response will decrease. As a consequence, the optimum between two contradictory requirements for application in the body must be found.
  • a three-dimensional polymeric network formed from the reaction of a trifunctional branched polymer with at least three arms substantially similar in molecular weight and a second precursor molecule that is at least a bifunctional molecule.
  • the ratio of equivalent weight of the functional groups of the first and second precursor molecules is between 0.9 and 1.1.
  • the molecular weights of the arms of the first precursor molecule, the molecular weight of the second precursor molecule and the functionality of the branching points are selected such that the water content of the resulting polymeric network is between the equilibrium weight % and 92 weight % of the total weight of the polymeric network after completion of water uptake.
  • the water content is between 93 and 95 weight % of the total weight of the polymeric network and the water after completion of water uptake.
  • Completion of water uptake can be achieved either when the equilibrium concentration is reached or when the space available in the biomaterial does not allow for further volume increase. It is therefore preferred to choose the starting concentrations of the precursor components to be as low as possible. This is true for all swellable matrices but in particular for those matrices which undergo cell-mediated degradation and do not contain hydrolytically degradable linkages in the polymeric network.
  • the balance between gelling time and low starting concentration in particular for hydrolytically non-degradable gels should to be optimized based on the structure of the precursor molecules.
  • the molecular weight of the arms of the first precursor molecule, the molecular weight of the second precursor molecule and the degree of branching, i.e. the functionality of the branching points have to be adjusted accordingly.
  • the actual reaction mechanism has a minor influence on this interplay.
  • the first precursor molecule a three or four arm polymer with a functional group at the end of each arm and is the second precursor molecule a linear bifunctional molecule, preferably a peptide containing at least two cysteine groups
  • the molecular weight of the arms of the first precursor molecule and the molecular weight of the second precursor molecule are preferably chosen such that the links between the branching points after formation of the network have a molecular weight in the range of between 10 to 13 kD (under the conditions that the links are linear, not branched) , preferably between 11 and 12 kD.
  • the molecular weight of the links between the branching points is preferably increased to a molecular weight of between 18 to 24 kDa.
  • the branching degree of the second precursor molecule is increased from linear to a three or four arm precursor component the molecular weight, i.e. the length of the links increase accordingly.
  • a composition is chosen including as the first precursor molecule a trifunctional three arm 15kD polymer, i.e. each arm having a molecular weight of 5kD and as the second precursor molecule a bifunctional linear molecule of a molecular weight in the range of between 0.5 to 1.5kD, even more preferably around lkD.
  • the first and the second precursor component is a polyethylene glycol.
  • the first precursor component includes as functional groups conjugated unsaturated groups or bonds, most preferred an acrylate or a vinylsulfone and the functional groups of the second precursor molecule includes a nucleophilic group, preferably a thiol or amino groups.
  • the first precursor molecule is a four arm 20kD (each arm a molecular weight of 5kDa) polymer having functional groups at the terminus of each arm and the second precursor molecule is a bifunctional linear molecule of a molecular weight in the range of between 1 to 3 kD, preferred between 1.5 and 2 kD.
  • the first precursor molecule is a polyethylene glycol having vinylsulfone groups and the second precursor molecule is a peptide having cysteine groups.
  • the starting concentration of the sum of first and second precursor molecule ranges from the 8 to 11 weight %, preferably between 9 and 10 weight % of the total weight of the first and second precursor molecule and water (before formation of polymeric network), preferably between 5 and 8 weight % to achieve a gelling time of below 10 minutes.
  • These compositions have a gelling time at pH 8.0 and 37°C of about 3-10 minutes after mixing.
  • the matrix contains hydrolytically degradable linkages, formed e.g.
  • the network density with regard to cell infiltration is especially important in the beginning, but in aqueous environment the linkages will be hydrolyzed and the network will be loosened, to allow for cell infiltration.
  • the molecular weight of the interlinks i.e. the length of the links must increase.
  • Cells interact with their environment through protein-protein, protein- oligosaccharide and protein-polysaccharide interactions at the cell surface. Extracellular matrix proteins provide a host of bioactive signals to the cell.
  • Laminin a large multidomain protein (Martin, Annual Review of Cellular Biology, 3:57-85, 1987), has been shown to consist of three chains with several receptor-binding domains. These receptor-binding domains include the YIGSR (SEQ ID NO : 2) sequence of the laminin B 1 chain (Graf, et ah, Cell, 48:989-996, 1987; Kleinman, et ah, Archives of Biochemistry and Biophysics, 272:39-45, 1989; and Massia, et al, J.
  • YIGSR SEQ ID NO : 2
  • LRGDN SEQ ID NO: 3 of the laminin A chain (Ignatius, et ah, J of Cell Biology, 111:709-720, 1990)
  • PDGSR SEQ ID NO: 4 of the laminin Bl chain (Kleinman, et ah, 1989).
  • IKVAV SEQ ID NO: 5 of the laminin A chain (Tashiro, et ah, J.
  • peptide sites for cell adhesion are incorporated into the matrix, namely peptides that bind to adhesion- promoting receptors on the surfaces of cells into the biomaterials of the present invention.
  • adhesion promoting peptides can be selected from the group as described above.
  • Particularly preferred are the RGD sequence from fibronectin, the YIGSR (SEQ ID NO: 2) sequence from laminin.
  • Incorporation of cell attachment sites are a particularly preferred embodiment with synthetic matrices, but can also be included with some of the natural matrices.
  • the incorporation can be done, for example, simply by mixing a cysteine-containing cell attachment peptide with the precursor molecule including the conjugated unsaturated group, such as PEG acrylate, PEG acrylamide or PEG vinylsulfone a few minutes before mixing with the remainder of the precursor component including the nucleophilic group, such as thiol-containing precursor component. If the cell attachment site does not include a cysteine, it can be chemically synthesized to include one. During this first step, the adhesion-promoting peptide will become incorporated into one end of the precursor multiply functionalized with a conjugated unsaturation; when the remaining multithiol is added to the system, a cross- linked network will form.
  • the conjugated unsaturated group such as PEG acrylate, PEG acrylamide or PEG vinylsulfone
  • the concentration of adhesion sites covalently bound into the matrix significantly influences the rate of cell infiltration.
  • a RGD concentration range can be incorporated into the matrix with supports cell ingrowth and cell migration in an optimal way.
  • the optimal concentration range of adhesion sites like RGD is between 0.04 and 0.05 mM and even more preferably 0.05 mM in particular for a matrix having a water content between equilibrium concentration and 92 weight % after termination of water uptake.
  • Excellent bone healing results can be achieved by keeping the rate of cell migration and the rate of matrix degradation at fast.
  • a four arm polyethyleneglycol with a molecular weight of about 20,000 Da crosslinked with a protease degradation site GCRPQGIWGQDRC (SEQ ID NO: 8) and 0.050 mM GRGDSP (SEQ ID NO: 9) give particularly good cell ingrowth results and healing of bone defects.
  • the starting concentration of PEG and peptide below 10 weight % of the total weight of the molecules and water (before swelling).
  • the gels have a useable consistency and allow the osteoblasts and precursor cell to easily infiltrate the matrix.
  • the matrix material is preferably biodegradable by naturally present enzymes.
  • the rate of degradation can be manipulated by the degree of crosslinking and the inclusion of protease inhibitors in the matrix.
  • the PTH fusion peptide can be crosslinked and covalently bound to matrices through the crosslinkable substrate domain of the PTH fusion peptide.
  • the kind of substrate domain is dependent on the nature of the matrix.
  • transglutaminase substrate domains are particularly preferred.
  • the transglutaminase substrate domain may be a Factor XHIa substrate domain.
  • This Factor Xllla substrate domain may be include GAKDV (SEQ ID NO: 10), KKKK (SEQ ID NO: 11), or NQEQVSPL (SEQ ID NO: 12).
  • the coupling between the PTH and the transglutaminase substrate domain can be performed by chemical synthesis.
  • the transglutaminase substrate domain can be a substrate for a transglutaminase other than Factor Xllla.
  • the most preferred Factor Xllla substrate domain has an amino acid sequence of NQEQVSPL (SEQ ID NO: 12) (herein referred to as "TG").
  • Other proteins that transglutaminase recognizes such as fibronectin, could be coupled to the transglutaminase substrate peptide.
  • the PTH fusion peptide or any other peptide to be incorporated must be synthesized with at least one additional cysteine goup (-SH) preferably at the N terminus of PTH as the crosslinkable substrate domain.
  • the cysteine can be either directly attached to the PTH or through a linker sequence.
  • the linker sequence can additionally include an enzymatically degradable amino acid sequence, so that the PTH can be cleaved from the matrix by enzymes in substantially the native form.
  • the free cysteine group reacts with the conjugated unsaturated group of the precursor component in a Michael type addition reaction.
  • the bondage to a synthetic matrix for PTH 1-34 is made possible by attaching an additional amino acid sequence to the N-terminus of PTH ⁇ -3 that contains at least one cysteine.
  • the thiol group of the cysteine can react with a conjugated unsaturated bond on the synthetic polymer to form a covalent linkage.
  • Possibility (a) only a cysteine is attached to the peptide, in possibility (b) an enzymatically degradable, in particular a plasmin degradable sequence is attached as linker between the cysteine and the peptide.
  • the sequence GYKNR SEQ ID NO: 15 between the first domain and the second domain, the cysteine, makes the linkage plasmin degradable.
  • the PTH fusion peptides may be further modified to contain a degradable site between the attachment site, i.e. the second domain (i.e. factor Xllla substrate domain or the cysteine) and the PTH , i.e. the first domain.
  • These sites may be degradable either by non-specific hydrolysis (i.e. an ester bond) or they may be substrates for specific enzymatic (either proteolytic or polysaccharide degrading) degradation.
  • These degradable sites allow the engineering of more specific release of PTH from matrices like fibrin gels. For example, degradation based on enzymatic activity allows for the release of PTH to be controlled by a cellular process rather than by diffusion of the factor through the gel.
  • the degradable site or linkage is cleaved by enzymes released from cells which invaded the matrix.
  • the degradation sites allow the PTH to be released with little or no modification to the primary peptide sequence, which may result in higher activity of the factor.
  • it allows the release of the factor to be controlled by cell specific processes, such as localized proteolysis, rather than diffusion from some porous materials. This allows factors to be released at different rates within the same material depending on the location of cells within the material. This also reduces the amount of total PTH needed, since its release is controlled by cellular processes.
  • Conservation of PTH and its bioavailability are distinct advantages of exploiting cell specific proteolytic activity over the use of diffusion controlled release devices. In one possible explanation for the strong healing of a bone defect with PTH covalently bound to a matrix, it is deemed important that the PTH is administered locally over an extended period of time (i.e.
  • Proteolytically degradable sites could include substrates for collagenase, plasmin, elastase, stromelysin, or plasminogen activators. Exemplary substrates are listed below. P1-P5 denote amino acids 1-5 positions toward the amino terminus of the protein from the site were proteolysis occurs. Pl'-P4' denote amino acids 1-4 positions toward the carboxy terminus of the protein from the site where proteolysis occurs. Table 2: Sample substrate sequences for protease.
  • an oligo-ester domain could be inserted between the first and the second domain This could be accomplished using an oligo-ester such as oligomers of lactic acid.
  • Non-enzymatic degradation substrate can consist of any linkage which undergoes hydrolysis by an acid or base catalyzed mechanism.
  • These substrates can include oligo-esters such as oligomers of lactic or glycolic acid. The rate of degradation of these materials can be controlled through the choice of oligomer.
  • D. PTH oligo-esters
  • PTH as used herein includes the human sequence of PTH 1-84 and all truncated, modified and allelic versions of PTH which exhibit bone formation properties when covalently bound to biodegradable natural or synthetic matrices.
  • Preferred truncated versions of PTH are PTH 1-38, PTH 1-34, PTH 1-31 or PTH 1-25. Most preferred is PTH 1-34.
  • the PTH is human PTH, although PTH from other sources, such as bovine PTH, may be suitable.
  • the matrix includes fibrin which is formed from fibrinogen, a calcium source and thrombin and the PTH fusion peptide will be incorporated within fibrin during coagulation.
  • PTH fusion peptide is designed as fusion peptide which include two domains, a first and a second one, one domain, the second one, is a substrate for a crosslinking enzyme such as Factor Xllla.
  • Factor Xllla is a transglutaminase that is active during coagulation.
  • This enzyme formed naturally from factor XIII by cleavage by thrombin, functions to attach fibrin chains to each other via amide linkages, formed between glutamine side chains and lysine side chains.
  • the enzyme also functions to attach other peptides to fibrin during coagulation, e.g. the cell attachment sites provided they include a factor Xllla too.
  • the sequence NQEQVSP (SEQ ID NO: 16)
  • NQEQVSP SEQ ID NO: 16
  • the PTH fusion peptide may be incorporated within fibrin during coagulation via a factor Xllla substrate.
  • the PTH fusion peptide which includes a first domain including the PTH, a second domain including a substrate domain for a crosslinking enzyme and optionally a degradation site between the first and the second domain can be incorporated into the fibrin gels using several different schemes.
  • the second domain includes a transglutaminase substrate domain and even more preferably it includes a Factor Xllla substrate domain.
  • the Factor Xllla substrate domain includes NQEQVSP (SEQ ID NO: 16).
  • the degradation site between the first and the second domain of the PTH fusion peptide can be an enzymatic degradation site as described previously.
  • the degradation site is cleavable by an enzyme selected from the group consisting of plasmin and matrix metalloproteinase.
  • K m and k cat of this enzymatic degradation site degradation could be controlled to occur either before or after the protein matrix and/or by utilizing similar or dissimilar enzymes to degrade the matrix, with the placement of the degradation site being tailored for each type of protein and application.
  • This PTH fusion peptide could be directly cross-linked into the fibrin matrix as described above. However, incorporating an enzymatic degradation site alters the release of the PTH during proteolysis.
  • the matrices can be used for repair, regeneration, or remodeling of tissues, and/or release of PTH, prior to or at the time of implantation. In some cases it will be desirable to induce crosslinking at the site of administration to conform the matrix to the tissue at the implantation site. In other cases, it will be convenient to prepare the matrix prior to implantation. Cells can also be added to the matrix prior to or at the time of implantation, or even subsequent to implantation, either at or subsequent to crosslinking of the polymer to form the matrix. This may be in addition to or in place of crosslinking the matrix to produce interstitial spacing designed to promote cell proliferation or in-growth.
  • the material is gelled in situ in or on the body.
  • the matrix can be formed outside the body and then applied in the preformed shape.
  • the matrix material can be made from synthetic or natural precursor components. Irrespective of the kind of precursor component used, the precursor components should be separated prior to application of the mixture to the body to prevent combination or contact with each other under conditions that allow polymerization or gelation of the components.
  • a kit which separates the compositions from each other may be used. Upon mixing under conditions that allow polymerization, the compositions form a bioactive factor supplemented three dimensional network.
  • gelling can occur quasi- instantaneously after mixing. Such fast gellation, makes injection, i.e. squeezing of the gelled material through the injection needle, almost impossible.
  • the matrix is formed from fibrinogen. Fibrinogen, through a cascade of various reactions gels to form a matrix, when brought in contact with thrombin and a calcium source at appropriate temperature and pH.
  • the three components, fibrinogen, thrombin, and the calcium source, should be stored separately. However, as long as at least one of the three components is kept separated the other two components can be combined prior to administration.
  • fibrinogen is dissolved (which may contain additionally aprotinin to increase stability) in a buffer solution at physiological pH (in a range from pH 6.5 to 8.0, preferably from pH 7.0 to 7.5) and stored separately from a solution of thrombin in a calcium chloride buffer (e.g.
  • the buffer solution for the fibrinogen can be a histidine buffer solution at a preferred concentration of 50 mM including additionally NaCl at a preferred concentration of 150 mM or TRIS buffer saline (preferably at a concentration of33mM).
  • a kit which contains a fusion protein, fibrinogen, thrombin, and a calcium source.
  • the kit may contain a crosslinking enzyme, such as Factor Xllla.
  • the fusion protein contains a bioactive factor, a substrate domain for a crosslinking enzyme and a degradation site between the substrate domain and bioactive factor.
  • the fusion protein may be present in either the fibrinogen or the thrombin solution.
  • the fibrinogen solution contains the fusion protein.
  • the solutions are preferably mixed by a two way syringe device, in which mixing occurs by squeezing the contents of both syringes through a mixing chamber and/or needle and/or static mixer.
  • both fibrinogen and thrombin are stored separately in lyophilised form. Either of the two can contain the fusion protein.
  • the buffer Prior to use, the tris or histidine buffer is added to the fibrinogen, the buffer may additionally contain aprotinin.
  • the lyophilized thrombin is dissolved in the calcium chloride solution.
  • the fibrinogen and the thrombin solutions are placed in separate containers/vials/syringe bodies and mixed by a two way connecting device, such as a two-way syringe.
  • the containers/vials/syringe bodies are bipartited thus having two chambers separated by an adjustable partition which is perpendicular to the syringe body wall.
  • One of the chambers contains the lyophilised fibrinogen or thrombin, while the other chamber contains an appropriate buffer solution.
  • the partition moves and releases the buffer into the fibrinogen chamber to dissolve the fibrinogen.
  • both bipartite syringe bodies are attached to a two way connecting device and the contents are mixed by squeezing them through the injection needle attached to the connecting device.
  • the connecting device contains a static mixer to improve mixing of the contents.
  • the fibrinogen is diluted eight fold and thrombin is diluted 20 fold prior to mixing. This ratio results in a gelation time of approximately one minute.
  • the matrix is formed from synthetic precursor components capable of undergoing a Michael addition reaction. Since the nucleophilic precursor component (the multithiol) only reacts with the multiacceptor component (the conjugated unsaturated group) at basic pH, the three components which have to be stored separately prior to mixing are: the base, the nucleophilic component and the multiacceptor component. Both the multiacceptor and the multithiol component are stored as a solutions in buffers. Both of the compositions can include the cell attachment site and additionally the bioactive molecule.
  • the first composition of the system can for example include the solution of the nucleophilic component and the second composition of the system can include the solution of the multiacceptor component. Either or both of the two compositions can include the base.
  • the multiacceptor and the multithiol can be included as solution in the first composition and the second composition can include the base. Connecting and mixing occurs in the same way as previously described for fibrinogen.
  • the bipartite syringe body is equally suitable for the synthetic precursor components. Instead of fibrinogen and thrombin the multiacceptor and multithiol components are stored in pulverized form in one of the chamber and the other chamber containes the basic buffer.
  • Example 1 Matrices containing covalently bound TGPTH. Synthesis of TGPTH
  • PTH 1-34-mer peptide showing similar activity to the whole protein, and proteins of this length can be synthesized by standard solid state peptide synthesis methods.
  • TGPTH TGPTH
  • TISSUCOL ® fibrin Eight mm holes that are 12 mm deep were created in the proximal and distal femur and humerus of sheep. These holes were filled with an in situ polymerizing fibrin gel. Defects were left empty, filled with TISSUCOL ® or TGPTH was added to TISSUCOL ® fibrin at 400 ⁇ g/mL before polymerization. In each example in which TISSUCOL ® was used, it was diluted four fold from the standard concentration available, leading to a fibrinogen concentration of 12.5 mg/mL.
  • the defects were allowed to heal for eight weeks. After this healing period, the animals were sacrificed, and the bone samples were removed and analyzed by micro computerized topography ( ⁇ CT). The percent of the defect volume filled with calcified bony tissue was then determined. When /052091
  • EXAMPLE 2 Healing response with modified PTH 1-34 attached to a fibrin matrix Materials
  • a fibrin gel was made from TISSUCOL ® Kit (Baxter AG, CH-8604 Volketswil/ZH) fibrin sealant precursor components.
  • the fibrinogen was diluted in sterile 0.03M Tris buffered solution (TBS, pH 7.4) to form an approximately 8mg/mL solution and the thrombin was diluted in sterile
  • the final concentration of fibrinogen was 1:8 original TISSUCOL ® formulation (about lOOmg/mL) and 1 : 160 original TISSUCOL ® thrombin concentration (about 500IE/mL).
  • a pre-determined amount of TG-pl-PTH 1-34 or TGPTH 1-34 was then added to the thrombin, and mixed to form a homogenous concentration.
  • the dilute precursors were mixed together by injecting the fibrinogen into the tube containing the thrombin. In case of the sheep drill defect (as described below) this mixture was then injected immediately into a drill defect created in sheep cancellous bone, where a fibrin gel formed within 1-5 minutes.
  • TG-pl- PTH 1-34 linkage plasmin degradable
  • the TG-pl-PTH 1-34 was made by chemical synthesis. Purification was accomplished through reversed phase HPLC (C18 column) by using a TFA as the counter ion which resulted in a final product that was a TFA salt. The purity of the TG-pl-PTH 1-34 was determined to be 95%.
  • the healing response was explored at both short (3 weeks) and long healing times (7 weeks) to determine if an enhancement in healing could be observed.
  • Rats were anaesthetized and the cranial bone was exposed.
  • the periosteum on the outer surface of the cranium was retracted so that it would not play a role in the healing process, and a single 8mm round defect was created.
  • This defect size was chosen as it has been previously determined that defects of 8 mm or larger do not spontaneously heal by themselves, and are critical size defects.
  • the defect was then fitted with a preformed fibrin matrix and the animal was allowed to heal for 3 and 7 weeks. The defect region was then explanted and analysed via radiology as well as histology. Results
  • TG-pl-PTH 1-3 was tested as well in a long bone defect model to test the effect of this hormone on healing bone.
  • 8mm cylindrically drill defects that were approximately 15 mm deep were placed in both the proximal and distal region of the femur and humerus bones. Since the defect was placed in the epiphysis of the long bones, the defect was surrounded by trabecular bone with a thin layer of cortical bone at the rim of the defect. These defects were then filled with an in situ polymerizing fibrin (about 750 ⁇ L) that contained various doses of TG-pl- PTH 1-34 . or TGPTH 1- 4 . Animals were allowed to heal for eight weeks and then were sacrificed.
  • TGPTH 1-34 was produced and purified similar to TG-pl-PTH 1-3 . Purity was determined to be 95%. TGPTH ⁇ -3 was tested at several concentrations that were similar to the concentrations of TG-pl-PTH 1-34 to compare efficacy. Finally, matrices were made in the presence of granular material, with either TGPTH ⁇ or TG-pl- PTH 1-3 . The granular material was a standard tricalcium phosphate/hydroxyapatite mixture which was embedded in the matrix during gelation. The effect of adding these granules on the efficacy of PTH ⁇ -34 was explored. As a control, unmodified fibrin was tested.
  • TG-pl-PTH ⁇ - was tested in a concentration series from 20-1000 ⁇ g/mL. For each dose tested, a significant increase in the healing response was observed. For example, when 100 ⁇ g/mL of TG-pl-PTH 1-3 was used, the healing rate was increased to almost 60%.
  • TGPTHj -34 was tested.
  • the use of TGPTH 1-34 also increased bone healing.
  • the use of 400 ⁇ g/mL improved the healing response to 40%, and 1000 ⁇ g/mL increased bony healing to 65%.
  • the addition of either modified PTH ⁇ -34 sequence resulted in a stronger healing response than the control.
  • Table 5 Healing of a sheep drill defect with PTH 1 . 34 bound to a fibrin matrix; Healing time 8 weeks
  • PEG vinyl sulfones were produced under argon atmosphere by reacting a dichloromethane solution of the precursor polymers (previously dried over molecular sieves) withNaH and then, after hydrogen evolution, with divinylsulfone (molar ratios: OH 1 : NaH 5: divinylsulfone 50). The reaction was carried out at room temperature for 3 days under argon with constant stirring. After the neutralization of the reaction solution with concentrated acetic acid, the solution was filtered through paper until clear. The derivatized polymer was isolated by precipitation in ice cold diethylether.
  • the product was redissolved in dichloromethane and reprecipitated in diethylether (with thoroughly washing) two times to remove all excess divinylsulfone. Finally, the product was dried under vacuum. The derivatization was confirmed with 1H NMR. The product showed characteristic vinyl sulfone peaks at 6.21 ppm (two hydrogens) and 6.97 ppm (one hydrogen). The degree of end group conversion was found to be 100%.
  • PEG acrylates were produced under argon atmosphere by reacting an azeotropically dried toluene solution of the precursor polymers with acryloyl chloride, in presence of friethylamine (molar ratios: OH 1: acryloyl chloride 2: friethylamine 2.2). The reaction proceeded with stirring overnight in the dark at room temperature. The resulting pale yellow solution was filtered through a neutral alumina bed; after evaporation of the solvent, the reaction product was dissolved in dichloromethane, washed with water, dried over sodium sulphate and precipitated in cold diethyl ether. Yield: 88%; conversion of OH to acrylate: 100% (from 1H-NMR analysis)
  • Peptide synthesis All peptides were synthesized on solid resin using an automated peptide synthesizer (9050 Pep Plus Synthesizer, Millipore, Framingham, USA) with standard 9-fluorenylmethyloxycarbonyl chemistry. Hydrophobic scavengers and cleaved protecting groups were removed by precipitation of the peptide in cold diethyl ether and dissolution in deionized water.
  • the peptides were redissolved in 0.03 M Tris-buffered saline (TBS, pH 7.0) and purified using HPLC (Waters; Milford, USA) on a size exclusion column with TBS, pH 7.0 as the running buffer.
  • MMP -sensitive gels formed by conjugate addition with a peptide-linked nucleophile and a PEG-linked conjugated unsaturation that allow proteolytic cell migration
  • the dissolved peptide Ac-GCGYGRGE>SRG-NH 2 (S ⁇ Q ID NO: 20) (in same buffer) were added to this solution.
  • the adhesion peptide was allowed to react for 30 minutes at 37°C.
  • the P ⁇ G-dithiol precursor was mixed with the above solution and gels were synthesized. The gelation occured within a few minutes, however, the crosslinking reaction was carried out for one hour at 37°C to guarantee complete reaction. Matrix formation by condensation reactions
  • MMP-sensitive gels formed by condensation reactions with a peptide X- linker containing multiple amines and a electrophilically active PEG that allow proteolytic cell migration
  • MMP-sensitive hydrogels were also created by conducting a condensation reaction between MMP-sensitive oligopeptide containing two MMP substrates and three Lys (Ac-GKGPQGIAGQKGPQGIAGQKG-NH 2 (SEQ ID NO: 22) and a commercially available (Shearwater polymers) difunctional double-ester PEG-N-hydroxysuccinimide (NHS-HBS-CM- PEG-CM-HBA-NHS).
  • an adhesion peptides e.g.
  • the peptide Ac-GCGYGRGDSRG-NH 2 (SEQ ID NO:20) was reacted with a small fraction of NHS-HBS-CM-PEG-CM-HBA-NHS and then this precursor was cross-linked to a network by mixing with the peptide Ac- (SEQ ID NO:22) bearing three ⁇ - amines (and one primary amine).
  • both components were dissolved in lOmM PBS at pH7.4 to give a 10% (w/w) solution and hydrogels were formed within less then one hour.
  • PEG-amine cross-linker and a electrophilically active PEG that allow non- proteolytic cell migration
  • Hydrogels were also formed by conducting a condensation reaction between commercially available branched PEG-amines (Jeffamines) and the same difunctional double-ester PEG-N-hydroxysuccinimide (NHS-HBS-CM- PEG-CM-HBA-NHS).
  • the adhesion peptides e.g. the peptide Ac-GCGYGRGDSRG-NH ) (SEQ ID NO:20) was reacted with a small fraction of NHS-HBS-CM-PEG-CM-HBA-NHS and then this precursor was cross-linked to a network by mixing with the multiarm PEG-amine.
  • both components were dissolved in lOmM PBS at ⁇ H7.4 to give a 10% (w/w) solution and hydrogels were formed within less then one hour.
  • the polymeric network was formed from a four-arm branched PEG functionalized with four vinylsulfone endgroups of a molecular weight of 20kD (molecular weight of each of the arms 5kD) and dithiol peptide of the following sequence Gly- Cys-Arg-Asp-(Gly-Pro-Gln-Gly-Ile-Tr ⁇ -Gly-Gln)-As ⁇ -Arg-Cys-Gly (SEQ ID NO:21). Both precursor components were dissolved in 0.3 M Triethanolamine.
  • the starting concentration of the functionalized PEG (first precursor molecule) and the dithiol peptide (second precursor molecule) were varied. In one case the concentration was 12.6 weight % of the total weight of the composition (first and second precursor component + triethanolamine solution). The 12.6 weight % corresponds to a 10 weight % solution when calculated on bases of only the first precursor component. (100 mg/mL first precursor molecule). The second staring concentration was 9.5 weight % of the total weight of the composition (first and second precursor component + triethanolamine solution) which corresponds to 7.5 weight % on basis of only the first precursor molecule (75 mg/mL first precursor molecule) of total weight .
  • PTH 1-34 fusion peptide was tested in a synthetic gel as well in the sheep drill defect model exactly as described for the fibrin matrices.
  • a hydrogel network was created by mixing together acrylated 4arm polyethylene glycol, MW 15,000 (Peg 4*15 Acr) with a linear polyethylene gylcol dithiol of MW 3400. Through a Michael type reaction, when the two components are mixed in a buffer of 0.3M Triethanolamine at pH 8.0, the resulting thiolates that are formed at this pH can then react with the conjugated unsaturation of the acrylate to create a covalent bond. By mixing together multifunctional precursors, such that the combined multifunctionality is greater than or equal to five, a hydrogel is formed.
  • bioactive factors can be added to the matrix through an identical reaction scheme.
  • bioactive factors including cell adhesion motives or morphogenic or mitogenic factors could be bound to the matrix by adding a cysteine, the thiol containing amino acid, to the sequence.
  • a cysteine to the cell adhesion sequence, RGD, and more specifically, RGDSP (SEQ ID NO: 23) as well as to the PTH 1-34 sequence and both were bound to the mafrix via the acrylates in the crosslinker.
  • RGD cell adhesion sequence
  • RGDSP SEQ ID NO: 23
  • these newly formed hydrogels then have numerous esters near a thiol, which has been shown to be hydrolytically unstable. This instability allows the gels to slow degrade and be replaced by newly formed tissue.

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Abstract

Dans la présente invention, des protéines sont introduites dans des matrices de protéines ou de polysaccharides destinées à être utilisées pour réparer, régénérer et/ou remodeler les tissus et/ou apporter des médicaments. Ces protéines peuvent être introduites de façon à ce qu'elles soient libérées par la dégradation de la matrice par une action enzymatique et/ou par diffusion. Comme le démontrent les exemples, un des procédés consiste à lier l'héparine à la matrice par des procédés de liaison covalente ou non covalente afin de former une matrice d'héparine. L'héparine lie ensuite de manière non covalente des facteurs de croissance liant l'héparine à la matrice protéique. Dans une variante, une peut construire une protéine qui contient une région de réticulation telle qu'un substrat de facteur XIIIa et la séquence de protéines natives. Il est particulièrement intéressant d'incorporer des liaisons dégradables entre la matrice et les facteurs bioactifs lorsqu'un apport de médicament de longue durée est souhaité, par exemple, en cas de régénération nerveuse lorsqu'il est souhaitable de varier la vitesse de libération du médicament dans l'espace en fonction de la régénération, par exemple, rapidement à proximité de l'interface avec les tissus vivants et plus lentement dans une zone plus profonde de la région de la lésion. D'autres avantages concernent la dose totale de médicament qui est plus faible dans le système d'apport et la régulation dans l'espace de la libération qui permet de libérer un plus grand pourcentage du médicament au moment où l'activité cellulaire est à son maximum.
PCT/US2002/041114 2001-12-18 2002-12-18 Matrices proteiques modifiees de facteur de croissance pour des applications en genie tissulaire WO2003052091A1 (fr)

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MXPA04006021A MXPA04006021A (es) 2001-12-18 2002-12-18 Matrices de proteina modificada con factor de crecimiento para ingenieria de tejidos.
EP02792510A EP1465989B1 (fr) 2001-12-18 2002-12-18 Matrices proteiques modifiees de facteur de croissance pour des applications en genie tissulaire
DE60225185T DE60225185T2 (de) 2001-12-18 2002-12-18 Wachstumsfaktor-modifizierte proteinmatrizes zur geweberekonstruktion (tissue engineering)
BRPI0215192A BRPI0215192B8 (pt) 2001-12-18 2002-12-18 peptídeo de fusão, kit e matriz que compreendem o mesmo, e método para criar uma matriz
AU2002358272A AU2002358272B2 (en) 2001-12-18 2002-12-18 Growth factor modified protein matrices for tissue engineering
JP2003552958A JP4560291B2 (ja) 2001-12-18 2002-12-18 組織操作のための成長因子改変タンパク質マトリクス
CA002470419A CA2470419A1 (fr) 2001-12-18 2002-12-18 Matrices proteiques modifiees de facteur de croissance pour des applications en genie tissulaire
KR1020047009700A KR100925070B1 (ko) 2001-12-18 2002-12-18 성장인자로 변형된 조직 엔지니어링용 단백질 메트릭스
NO20043031A NO331726B1 (no) 2001-12-18 2004-07-15 Fusjonspeptid som omfatter et forste domene som omfatter paratyroidhormon (PTH) og et andre domene som omfatter et substratdomene, sett og matriks som omfatter fusjonspeptidet, og fremgangsmate til a fremstille en matriks
HK04110140A HK1067147A1 (en) 2001-12-18 2004-12-22 Growth factor modified protein matrices for tissueengineering

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US10/024,918 US20020168718A1 (en) 1997-04-03 2001-12-18 Enzyme-mediated modification of fibrin for tissue engineering
US10/024,918 2001-12-18
EPPCT/EP02/12458 2002-11-07
PCT/EP2002/012458 WO2003040235A1 (fr) 2001-11-07 2002-11-07 Matrice synthetique de croissance cellulaire interne et de regeneration tissulaire controlees
US10/323,046 US7601685B2 (en) 1998-08-27 2002-12-17 Growth factor modified protein matrices for tissue engineering
US10/325,021 2002-12-18

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WO2003052091A8 WO2003052091A8 (fr) 2003-08-07

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AT (1) ATE386545T1 (fr)
AU (2) AU2002358272B2 (fr)
BR (1) BRPI0215192B8 (fr)
CA (1) CA2470419A1 (fr)
DE (1) DE60225185T2 (fr)
ES (1) ES2301697T3 (fr)
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WO2006072622A2 (fr) * 2005-01-06 2006-07-13 Kuros Biosurgery Ag Matrices enrichies pour la reparation des fractures osseuses
WO2006072623A1 (fr) * 2005-01-06 2006-07-13 Kuros Biosurgery Ag Traitement local de deficit osseux au moyen d'une matrice liberant de la bmp ou de la pth
EP1862170A1 (fr) 2004-12-10 2007-12-05 Straumann Holding AG Formulation de protéine
US7351423B2 (en) 2004-09-01 2008-04-01 Depuy Spine, Inc. Musculo-skeletal implant having a bioactive gradient
JP2008523047A (ja) * 2004-12-10 2008-07-03 シュトラウマン・ホールディング・アクチェンゲゼルシャフト 新規なタンパク質配合物
US7423013B2 (en) 2004-12-10 2008-09-09 Straumann Holding Ag Protein formulation
WO2009047361A2 (fr) * 2007-10-12 2009-04-16 Kuros Biosurgery Ag Compositions radio-opaques injectables pour une augmentation de tissu
WO2011025957A3 (fr) * 2009-08-28 2011-07-07 Ecole Polytechnique Federale De Lausanne Protéines de fusion tg-aprotinine et matrices comprenant celles-ci
WO2012123028A1 (fr) 2011-03-16 2012-09-20 Kuros Biosurgery Ag Formulation pharmaceutique destinée à être utilisée dans une fusion des vertèbres
US8450273B2 (en) 2007-04-09 2013-05-28 The Board Of Trustees Of The University Of Arkansas Fusion proteins of collagen-binding domain and parathyroid hormone
US8469233B2 (en) 2008-04-18 2013-06-25 Kuros Biosurgery Ag Dispensing device, kit containing the device, and method of operating the device
US8575101B2 (en) 2005-01-06 2013-11-05 Kuros Biosurgery Ag Supplemented matrices for the repair of bone fractures
US9526765B2 (en) 2012-02-09 2016-12-27 The Kitasato Institute Delivery of therapeutic agents by a collagen binding protein
US9579273B2 (en) 2011-12-14 2017-02-28 The Kitasato Institute Delivery of therapeutic agents by a collagen binding protein
EP3536353A1 (fr) 2018-03-09 2019-09-11 Kuros Biosurgery AG Procédé et kits de production d'une matrice de fibrine
US11624060B2 (en) 2017-02-10 2023-04-11 The Board Of Trustees Of The University Of Arkansas Collagen-binding agent compositions and methods of using the same

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EP2670856B1 (fr) * 2011-02-03 2018-06-27 Northeastern University Procédés et compositions pour la capture et la libération hautement spécifiques de matières biologiques
US9790264B2 (en) 2012-06-25 2017-10-17 The Brigham And Women's Hospital, Inc. Compounds and methods for modulating pharmacokinetics
US9421245B2 (en) * 2012-06-25 2016-08-23 The Brigham And Women's Hospital, Inc. Targeted therapeutics
WO2017042301A1 (fr) * 2015-09-09 2017-03-16 ETH Zürich Hydrogels macroporeux injectables

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US7351423B2 (en) 2004-09-01 2008-04-01 Depuy Spine, Inc. Musculo-skeletal implant having a bioactive gradient
US7423013B2 (en) 2004-12-10 2008-09-09 Straumann Holding Ag Protein formulation
JP2011219492A (ja) * 2004-12-10 2011-11-04 Straumann Holding Ag 新規なタンパク質配合物
US7985845B2 (en) 2004-12-10 2011-07-26 Straumann Holding Ag Protein formulation
EP1862170A1 (fr) 2004-12-10 2007-12-05 Straumann Holding AG Formulation de protéine
JP2008523047A (ja) * 2004-12-10 2008-07-03 シュトラウマン・ホールディング・アクチェンゲゼルシャフト 新規なタンパク質配合物
EP2329832A1 (fr) 2004-12-10 2011-06-08 Straumann Holding AG Formulation de protéines
WO2006067221A2 (fr) * 2004-12-22 2006-06-29 Kuros Biosurgery Ag Biomateriaux synthetiques comprenant des facteurs bioactifs incorpores au moyen de liaisons degradables par voie enzymatique
WO2006067221A3 (fr) * 2004-12-22 2006-09-28 Kuros Biosurgery Ag Biomateriaux synthetiques comprenant des facteurs bioactifs incorpores au moyen de liaisons degradables par voie enzymatique
JP2008526810A (ja) * 2005-01-06 2008-07-24 クロス・バイオサージェリー・アクチェンゲゼルシャフト 骨折修復のための強化（ｓｕｐｐｌｅｍｅｎｔｅｄ）マトリックス
JP2008526811A (ja) * 2005-01-06 2008-07-24 クロス・バイオサージェリー・アクチェンゲゼルシャフト Ｂｍｐまたはｐｔｈを放出するマトリックスを用いた骨欠陥の局所治療
EP3111966A1 (fr) 2005-01-06 2017-01-04 Kuros Biosurgery AG Matrices enrichies pour la réparation des fractures osseuses
EP2316497A3 (fr) * 2005-01-06 2014-05-07 Kuros Biosurgery AG Matrices supplémentées pour la réparation de fractures osseuses
EP2316497A2 (fr) 2005-01-06 2011-05-04 Kuros Biosurgery AG Matrices supplémentées pour la réparation de fractures osseuses
US8318674B2 (en) 2005-01-06 2012-11-27 Kuros Biosurgery Ag Local treatment of bone defects
US8575101B2 (en) 2005-01-06 2013-11-05 Kuros Biosurgery Ag Supplemented matrices for the repair of bone fractures
WO2006072622A3 (fr) * 2005-01-06 2006-11-23 Kuros Biosurgery Ag Matrices enrichies pour la reparation des fractures osseuses
WO2006072623A1 (fr) * 2005-01-06 2006-07-13 Kuros Biosurgery Ag Traitement local de deficit osseux au moyen d'une matrice liberant de la bmp ou de la pth
WO2006072622A2 (fr) * 2005-01-06 2006-07-13 Kuros Biosurgery Ag Matrices enrichies pour la reparation des fractures osseuses
US8450273B2 (en) 2007-04-09 2013-05-28 The Board Of Trustees Of The University Of Arkansas Fusion proteins of collagen-binding domain and parathyroid hormone
US10202434B2 (en) 2007-04-09 2019-02-12 The Board Of Trustees Of The University Of Arkansas Fusion proteins of collagen-binding domain and parathyroid hormone
US9062300B2 (en) 2007-04-09 2015-06-23 National University Corporation Kagawa University Fusion proteins of collagen-binding domain and parathyroid hormone
US9528099B2 (en) 2007-04-09 2016-12-27 Ochsner Clinic Foundation Fusion proteins of collagen-binding domain and parathyroid hormone
US10519213B2 (en) 2007-04-09 2019-12-31 The Board Of Trustees Of The University Of Arkansas Fusion proteins of collagen-binding domain and parathyroid hormone
US10358471B2 (en) 2007-04-09 2019-07-23 The Board Of Trustees Of The University Of Arkansas Fusion proteins of collagen-binding domain and parathyroid hormone
WO2009047361A3 (fr) * 2007-10-12 2009-07-30 Kuros Biosurgery Ag Compositions radio-opaques injectables pour une augmentation de tissu
WO2009047361A2 (fr) * 2007-10-12 2009-04-16 Kuros Biosurgery Ag Compositions radio-opaques injectables pour une augmentation de tissu
US8469233B2 (en) 2008-04-18 2013-06-25 Kuros Biosurgery Ag Dispensing device, kit containing the device, and method of operating the device
WO2011025957A3 (fr) * 2009-08-28 2011-07-07 Ecole Polytechnique Federale De Lausanne Protéines de fusion tg-aprotinine et matrices comprenant celles-ci
US10589001B2 (en) 2011-03-16 2020-03-17 Kuros Biosurgery Ag Pharmaceutical formulation for use in spinal fusion
WO2012123028A1 (fr) 2011-03-16 2012-09-20 Kuros Biosurgery Ag Formulation pharmaceutique destinée à être utilisée dans une fusion des vertèbres
US9579273B2 (en) 2011-12-14 2017-02-28 The Kitasato Institute Delivery of therapeutic agents by a collagen binding protein
US11001820B2 (en) 2011-12-14 2021-05-11 The Board Of Trustees Of The University Of Arkansas Delivery of therapeutic agents by a collagen binding protein
US11279922B2 (en) 2011-12-14 2022-03-22 The Board Of Trustees Of The University Of Arkansas Delivery of therapeutic agents by a collagen binding protein
US10213488B2 (en) 2012-02-09 2019-02-26 The Board Of Trustees Of The University Of Arkansas Delivery of therapeutic agents by a collagen binding protein
US9526765B2 (en) 2012-02-09 2016-12-27 The Kitasato Institute Delivery of therapeutic agents by a collagen binding protein
US11624060B2 (en) 2017-02-10 2023-04-11 The Board Of Trustees Of The University Of Arkansas Collagen-binding agent compositions and methods of using the same
EP3536353A1 (fr) 2018-03-09 2019-09-11 Kuros Biosurgery AG Procédé et kits de production d'une matrice de fibrine
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US11266762B2 (en) 2018-03-09 2022-03-08 Kuros Biosurgery Ag Methods and kits for producing a fibrin matrix

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DE60225185D1 (de) 2008-04-03
AU2002358272B2 (en) 2009-01-22
JP2005517658A (ja) 2005-06-16
WO2003052091A8 (fr) 2003-08-07
AU2002358272A1 (en) 2003-06-30
CA2470419A1 (fr) 2003-06-26
BRPI0215192B1 (pt) 2016-03-22
JP4560291B2 (ja) 2010-10-13
ES2301697T3 (es) 2008-07-01
BR0215192A (pt) 2005-04-26
MXPA04006021A (es) 2005-08-19
AU2009201588B2 (en) 2011-02-24
ATE386545T1 (de) 2008-03-15
BRPI0215192B8 (pt) 2021-07-27
AU2009201588A1 (en) 2009-05-14
DE60225185T2 (de) 2009-02-19
JP2009102383A (ja) 2009-05-14

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